WO2003055380A2 - Appareil d'eclairage d'aberroscope, et procede - Google Patents

Appareil d'eclairage d'aberroscope, et procede Download PDF

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Publication number
WO2003055380A2
WO2003055380A2 PCT/US2002/040067 US0240067W WO03055380A2 WO 2003055380 A2 WO2003055380 A2 WO 2003055380A2 US 0240067 W US0240067 W US 0240067W WO 03055380 A2 WO03055380 A2 WO 03055380A2
Authority
WO
WIPO (PCT)
Prior art keywords
wavefront
eye
patient
component
retina
Prior art date
Application number
PCT/US2002/040067
Other languages
English (en)
Other versions
WO2003055380A3 (fr
Inventor
Ronald J. Martino
David F. Prelewitz
Kevin Kearney
Original Assignee
Bausch & Lomb Incorporated
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Bausch & Lomb Incorporated filed Critical Bausch & Lomb Incorporated
Priority to KR1020047009686A priority Critical patent/KR100925526B1/ko
Priority to EP02805942A priority patent/EP1458280B1/fr
Priority to JP2003555959A priority patent/JP4206338B2/ja
Priority to AU2002357237A priority patent/AU2002357237B2/en
Priority to DE60223075T priority patent/DE60223075T2/de
Priority to CA002471037A priority patent/CA2471037C/fr
Publication of WO2003055380A2 publication Critical patent/WO2003055380A2/fr
Publication of WO2003055380A3 publication Critical patent/WO2003055380A3/fr
Priority to HK05109000.4A priority patent/HK1076996A1/xx

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A61B3/14—Arrangements specially adapted for eye photography
    • A61B3/15—Arrangements specially adapted for eye photography with means for aligning, spacing or blocking spurious reflection ; with means for relaxing
    • A61B3/156—Arrangements specially adapted for eye photography with means for aligning, spacing or blocking spurious reflection ; with means for relaxing for blocking
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A61B3/103—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for determining refraction, e.g. refractometers, skiascopes

Definitions

  • the present invention pertains to the field of wavefront sensing and, particularly, to an improved ophthalmic aberrometer and method for retinal illumination.
  • a wavefront sensor often referred to as an aberrometer (which terms will.be used interchangeably herein), is a device that measures a difference in the optical path of light between a deformed wavefront and an ideal or reference wavefront.
  • a properly processed measurement yields values for various aberrations in the optical system that the light propagates through.
  • Recent attention has focused on the design and use of wavefront sensors for measuring the aberrations of the eye with the goal of improving visual quality.
  • Williams' U.S. patent 5,777,719 describes a Shack-Hartmann type wavefront sensor that can be used to measure, among other parameters, higher-order ocular aberrations.
  • Shack-Hartmann wavefront sensors are characterized by a microlens (lenslet) array for imagining the light reflection from the retina into an array of spots on a detector.
  • the resulting spot image array is displaced from the regular array resulting from an unaberrated optical system.
  • These displacements of the spots are used to determine the wavefront slope at each spot location and this information is typically used to determine the coefficients of Zernike polynomials which represent different orders and modes of the wavefront aberrations.
  • Other types of aberrometers include the spatially resolved refractometer based on the Schemer optometer, those based on the Tscherning principle, skiascopic systems, scanning systems of the Tracey technology type, raytracing devices, and others.
  • a retinal illumination source typically a light emitting diode, a superluminescent diode (SLD), a diode laser (typically operated below threshold) or, another, preferably partially-coherent source that produces a point source on the patient's retina.
  • SLD superluminescent diode
  • diode laser typically operated below threshold
  • another, preferably partially-coherent source that produces a point source on the patient's retina.
  • the eye illumination focus on the eye's fovea so that the ultimate wavefront measurement represents aberrations at the fovea, the highest resolution portion of the retina. Illumination that covers an area larger than the fovea will produce less accurate aberration values.
  • patient refractive error is the largest optical defect to contend with in aberrometer wavefront measurement. Such error limits the measurement range of the aberrometer.
  • the typical ophthalmic patient will have an uncorrected defocus in a wide range between +15 diopters (D). This means that the eye will focus light some distance either in front of or behind the retinal plane, producing blurry images on the retina when this value is different from zero.
  • D diopters
  • Lasers used herein throughout to refer to the retinal illumination source
  • the retinal illumination source typically have beam diameters of about 1.5mm.
  • the fovea of the eye is also about 1.5mm in diameter, any defocus power in the eye will inhibit a tight match between the illuminating beam and the retinal target.
  • Aberrometers are generally constructed such that their optical systems include refocusing means to account for the patient's refractive power, and also, so that the wavefront image spots are in focus on the wavefront detector.
  • the refocus of the laser beam can be accomplished by injecting it in a position in the aberrometer optical system so that the refocus occurs with the correction of the patient's defocus.
  • a separate focussing optical path can be provided for the illumination light.
  • Another concern for accurate wavefront measurement is the compensation of refractive errors on the input side of aberration measurement.
  • One approach for providing a small illumination spot on the fovea was to create a best focus by geometrically correcting the input light by either adding or subtracting optical power from a plane wave. Hence, the input light would diverge or converge to compensate for myopia or hyperopia, respectively.
  • the input beam In a myopic eye with a small pupil diameter, however, the input beam is diverging before intercepting the cornea, and the input light profile can take on a significant aberration signature prior to striking the retina. This can seriously degrade the intensity profile distribution which can interject error in localizing (centroiding) the imaged spot on the fovea and, in turn, in the wavefront reconstruction.
  • a very small input beam will suffer from diffraction effects and reduce measurement range.
  • the invention is generally directed to illuminating a patient's retina for making a wavefront measurement with an illumination beam having a beam characteristic, e.g., diameter or profile, that a) eliminates the need to refocus between the source and the patient's cornea, and b) which maintains a beam spot area on the fovea that is smaller than the diffraction limit of a wavefront imaging component over a defocus range typically encountered in the patient population; i.e., between about -12D to +10D and, preferably, between -12D (+0.25D) to +6D (+0.25D).
  • An embodiment of the invention is directed to an improved wavefront sensing device.
  • the improvement is characterized by the aberrometer having an optical path between a retinal illumination source and a patient's eye containing no refractive, diffractive, or other phase altering components.
  • the effective use of Gaussian wave propagation will provide a tight beam waist and a Rayleigh range that extends over a specified refractive error range.
  • the beam diameter of the illumination beam at the patient's anterior cornea is less than 1mm.
  • the retinal illumination source is preferably a 780nm diode laser assembly including an integrated collimating lens; alternatively, a SLD or other source producing coherent or semi- coherent light of a suitable wavelength, plus fixed lens component, may provide the appropriate illumination size and profile.
  • the wavefront imaging component for imaging at least a portion of the unknown wavefront on a detector is preferably a lenslet of o microlens array of a Shack-Hartmann sensor.
  • a method of making a more accurate wavefront measurement of a patient's eye comprises illuminating the patient's retina with an illumination beam over an optical path between the source and the patient's eye that is free of any refracting, diffracting or phase altering components.
  • An aspect of this embodiment involves providing foveal illumination with a beam diameter that is less than a diffraction limit value of an imaging component that images a portion of the wavefront on a detector over a refractive focus range of the patient's eye between about -12D to +6D.
  • the method further entails providing a Gaussian illumination beam having a Rayleigh range that is greater than the refractive focus range of the patient's eye between about -12D to +6D.
  • Figure 1 is an optical schematic of a wavefront sensor according to an embodiment of the invention
  • Figure 2 is a schematic diagram showing an illumination component and output retinal illumination beam over a typical range of defocus in the eye according to an embodiment of the invention
  • Figure 3 is an optical schematic of an off-axis illumination system according to the invention.
  • Figure 4 is an optical schematic of an off-axis illumination system according to another embodiment of the invention.
  • FIG. 1 is an illustration of an improved wavefront sensor in the form of a Shack-Hartmann aberrometer 10 according to. an embodiment of the invention. It will be appreciated that the invention is not limited to a Shack-Hartmann aberrometer, but in fact applies to all aberrometers and wavefront sensing methods that require point source retinal illumination and wavefront imaging for aberration analysis. Generically, an aberrometer 10 requires an optical head, a data acquisition, storage and processing system for detecting, measuring and displaying wavefront aberration data, and interlinking electronics and software.
  • the laser is a 785nm Blue Slcy Research CircuLaser Diode (PS 108-00) that provides a circularized beam with a total divergence of 10 degrees.
  • the collimating lens 72 is a Geltech molded asphere 350200 that was chosen due to its short focal length and reasonable cost (available from Thorlabs already coated and mounted). The focal length is chosen so that the laser beam diameter incident on the cornea is very small, preferably lmm or less, to avoid effects of wavefront error of the eye on the input pass.
  • the model contains the laser source 70, the collimating lens 72, and a model (Gullstrand) of a normal eye 75.
  • the axial distance from the second surface 72b of the collimating lens 72 to the anterior cornea 74 is 104.92mm.
  • the distance from the laser 70 to the collimating lens 72 is 0.735mm.
  • Gaussian beam propagation is used to simulate the behavior of the laser beam with a Gaussian cross sectional intensity distribution. A 2 micron input beam waist was assumed.
  • Ray trace analysis shows the beam diameter at the cornea at roughly 0.46mm, well within the goal of lmm or less.
  • the size of the spot on the retina, 64 microns, corresponds to an angular range of +/-0.11 degrees exiting the eye. This is calculated
  • the trombone for the specific design at hand is made up of two lenses with focal length ratio of 1.075, thus increasing the angle by that factor.
  • the distance from the back of the eye lens 77 to the retina 76 was lengthened to simulate nearsightedness and shortened to simulate farsightedness.
  • the spot size on the retina is even smaller, meaning that for this length eyeball, the retina is closer to the minimum beam waist position.
  • the spot on the retina could be as large as 94 microns diameter. This corresponds to 37 micron spots at the wavefront sensor.
  • the distance from the laser 70 to the collimating lens 72 can be varied to place the minimum beam waist on the retina 76 for a different case. The solution described above minimizes the spot size for the 0D case.
  • the spot for the - 12D patient can get as small as 10 microns, but not without the spot for the +6 diopter patient growing to 95 microns.
  • magnification is an important aspect to this approach.
  • the lenslet array is an optical system, it will always magnify (or de-magnify) from object to image; in this case, the spot projected onto the retina to the camera sensor.
  • the angular spread of the blur spot (Airy spot or the diffraction limited spot) of the lenslet must always be greater than the subtended angle of the object (the retinal spot).
  • the laser injection optics and the wavefront camera imaging optics the lenslet, and to a much lesser degree, the trombone optics
  • the illumination component 12 is positioned off- axis relative to the patient's eye 32 as shown schematically in Figure 3.
  • Figure 3 shows an overview of a basic Shack-Hartmann aberrometer system 100 for off-axis illumination of the retina R.
  • the laser component 12 emits beam 40 towards beamsplitter 16a.
  • the illumination component 12 and beamsplitter 16a are positioned such that the light beam 40 impinges the eye 32 off of the optical axis A of the eye.
  • a light beam 41 reflected from the cornea 42 of the eye is reflected off of the optical axis A.
  • the remaining light forms a laser beacon B on the retina R of the eye 32.
  • the eye's optics propagate a light beam 50 out of the eye that passes through the beamsplitter 16a. Beam 50 then passes through a lens 56, a stop 58 which passes the beam 50 while blocking the beam 41 reflected from the cornea, and a lens 60 to a Hartmann-Shack detector 62.
  • the detector 62 comprises the lenslet array 18 to focus the beam 50 as an array of light spots onto a CCD or other suitable two-dimensional detector 22.
  • the beam 40 will exhibit the Gaussian characteristics described above for maintaining a retinal spot diameter that remains less than the diffraction limited spot size from the lenslets of the array 18.
  • the collimated laser beam 110 is offset laterally from the eye optical axis 112 to direct corneal back reflections 114 out of the wavefront-sensing path.
  • an offset, Y of between about 0.5mm to lmm is suitable with a preferable offset being between about 0.7mm to lmm.
  • the lateral offset, Y be in the vertical direction (up or down in FIG. 4) due to the fact that the lateral position of the corneal vertex with respect to the geometric center of the pupil will vary from patient to patient. These differences can vary from 0.1mm up to 0.6mm; however, this difference is usually smaller in the vertical direction.
  • the position of the spot on the retina, R will vary as a function of refractive error. As shown in FIG. 4, for a lmm offset the variation could be up to 0.1mm for far-sighted patients, and 0.21mm for the most near-sighted patient. Angularly, these correspond to 0.34 degrees, and 0.7 degrees, respectively. Therefore, for patients with -4.7 to +4.0 diopters, the spot will be within the foveola (0.5 degree diameter), and all cases will be well within the fovea (5 degree diameter).
  • the presence of corneal back reflections at the detector can be detected and the operator can be alerted, accordingly, to make adjustment. This can be done by moving the laser in the instrument, or the entire instrument relative to the patient if it can be moved in sub- millimeter increments. As long as this difference is recorded, it should not upset the mapping of the measured wavefront to the patient's eye.
  • a method embodiment according to the invention is directed to obtaining a more accurate ocular wavefront aberration measurement with a wavefront-sensing device.
  • a retinal illumination source is provided having beam characteristics that eliminate any need to refocus the beam along a propagation path between the illumination source and a patient's eye.
  • the preferable beam characteristics are a Gaussian profile with a beam waist that is effectively of constant diameter over the refractive range of the eye, preferably over a refractive range between about +6D to - 12D.
  • a retinal illumination beam having a diameter on the eye's retina that is less than a diffraction limit value of an imaging component used to image a portion of the wavefront on a detector over a refractive focus range of the patient's eye between about -12D to +6D.

Abstract

L'invention concerne un dispositif de détection de front d'onde permettant de mesurer les aberrations oculaires, qui comprend, entre autres, un premier élément d'éclairage de la rétine et un second élément d'imagerie de front d'onde (par exemple, réseau de microlentilles pour capteur de front d'onde de Shack-Hartmann). Le premier élément comporte une source laser et une lentille collimatrice fixe. Selon une variante, l'invention concerne un dispositif amélioré ayant un trajet de faisceau établi entre le premier élément et l'oeil du patient, sans composantes de réfraction, de diffraction ou de modification de phase, pour la concentration du faisceau d'éclairage sur la rétine. Selon une autre variante, le premier élément fournit un faisceau dont le diamètre sur la rétine est inférieur à la limite de diffraction de l'élément d'imagerie de front d'onde, dans une gamme de foyers de réfraction de l'oeil du patient comprise entre environ -12D et +6D.
PCT/US2002/040067 2001-12-21 2002-12-13 Appareil d'eclairage d'aberroscope, et procede WO2003055380A2 (fr)

Priority Applications (7)

Application Number Priority Date Filing Date Title
KR1020047009686A KR100925526B1 (ko) 2001-12-21 2002-12-13 어베로미터 조명기기 및 방법
EP02805942A EP1458280B1 (fr) 2001-12-21 2002-12-13 Aberroscope
JP2003555959A JP4206338B2 (ja) 2001-12-21 2002-12-13 収差分析器イルミネーション装置および方法
AU2002357237A AU2002357237B2 (en) 2001-12-21 2002-12-13 Aberrometer illumination apparatus and method
DE60223075T DE60223075T2 (de) 2001-12-21 2002-12-13 Aberrometer
CA002471037A CA2471037C (fr) 2001-12-21 2002-12-13 Appareil d'eclairage d'aberroscope, et procede
HK05109000.4A HK1076996A1 (en) 2001-12-21 2005-10-12 A wavefront-sensing device

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US10/027,377 2001-12-21
US10/027,377 US6736509B2 (en) 2001-12-21 2001-12-21 Aberrometer illumination apparatus and method

Publications (2)

Publication Number Publication Date
WO2003055380A2 true WO2003055380A2 (fr) 2003-07-10
WO2003055380A3 WO2003055380A3 (fr) 2003-12-11

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PCT/US2002/040067 WO2003055380A2 (fr) 2001-12-21 2002-12-13 Appareil d'eclairage d'aberroscope, et procede

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US (1) US6736509B2 (fr)
EP (1) EP1458280B1 (fr)
JP (1) JP4206338B2 (fr)
KR (1) KR100925526B1 (fr)
CN (1) CN100469307C (fr)
AU (1) AU2002357237B2 (fr)
CA (1) CA2471037C (fr)
DE (1) DE60223075T2 (fr)
ES (1) ES2294206T3 (fr)
HK (1) HK1076996A1 (fr)
WO (1) WO2003055380A2 (fr)

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US7980698B2 (en) 2008-11-19 2011-07-19 Bausch & Lomb Incorporated Power-adjusted aberrometer
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Also Published As

Publication number Publication date
KR20040088033A (ko) 2004-10-15
EP1458280A2 (fr) 2004-09-22
JP4206338B2 (ja) 2009-01-07
AU2002357237A1 (en) 2003-07-15
CA2471037A1 (fr) 2003-07-10
DE60223075T2 (de) 2008-07-17
WO2003055380A3 (fr) 2003-12-11
HK1076996A1 (en) 2006-02-03
ES2294206T3 (es) 2008-04-01
CN1606422A (zh) 2005-04-13
AU2002357237B2 (en) 2007-07-05
JP2005514087A (ja) 2005-05-19
US20030117581A1 (en) 2003-06-26
DE60223075D1 (en) 2007-11-29
EP1458280B1 (fr) 2007-10-17
CN100469307C (zh) 2009-03-18
US6736509B2 (en) 2004-05-18
CA2471037C (fr) 2008-07-15
KR100925526B1 (ko) 2009-11-05

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